WO2013034611A1 - Fibre creuse - Google Patents

Fibre creuse Download PDF

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Publication number
WO2013034611A1
WO2013034611A1 PCT/EP2012/067353 EP2012067353W WO2013034611A1 WO 2013034611 A1 WO2013034611 A1 WO 2013034611A1 EP 2012067353 W EP2012067353 W EP 2012067353W WO 2013034611 A1 WO2013034611 A1 WO 2013034611A1
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WIPO (PCT)
Prior art keywords
membrane
graft copolymer
range
polyethersulfone
hollow fiber
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PCT/EP2012/067353
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English (en)
Inventor
Bernd Krause
Carina Zweigart
Markus Hornung
Ralf Menda
Original Assignee
Gambro Lundia Ab
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Publication of WO2013034611A1 publication Critical patent/WO2013034611A1/fr

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D67/00—Processes specially adapted for manufacturing semi-permeable membranes for separation processes or apparatus
    • B01D67/0002—Organic membrane manufacture
    • B01D67/0009—Organic membrane manufacture by phase separation, sol-gel transition, evaporation or solvent quenching
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D67/00—Processes specially adapted for manufacturing semi-permeable membranes for separation processes or apparatus
    • B01D67/0002—Organic membrane manufacture
    • B01D67/0009—Organic membrane manufacture by phase separation, sol-gel transition, evaporation or solvent quenching
    • B01D67/0011—Casting solutions therefor
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D67/00—Processes specially adapted for manufacturing semi-permeable membranes for separation processes or apparatus
    • B01D67/0002—Organic membrane manufacture
    • B01D67/0009—Organic membrane manufacture by phase separation, sol-gel transition, evaporation or solvent quenching
    • B01D67/0011—Casting solutions therefor
    • B01D67/00113—Pretreatment of the casting solutions, e.g. thermal treatment or ageing
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D69/00—Semi-permeable membranes for separation processes or apparatus characterised by their form, structure or properties; Manufacturing processes specially adapted therefor
    • B01D69/08—Hollow fibre membranes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D69/00—Semi-permeable membranes for separation processes or apparatus characterised by their form, structure or properties; Manufacturing processes specially adapted therefor
    • B01D69/08—Hollow fibre membranes
    • B01D69/087—Details relating to the spinning process
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D71/00—Semi-permeable membranes for separation processes or apparatus characterised by the material; Manufacturing processes specially adapted therefor
    • B01D71/06—Organic material
    • B01D71/44—Polymers obtained by reactions only involving carbon-to-carbon unsaturated bonds, not provided for in a single one of groups B01D71/26-B01D71/42
    • B01D71/441—Polyvinylpyrrolidone
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D71/00—Semi-permeable membranes for separation processes or apparatus characterised by the material; Manufacturing processes specially adapted therefor
    • B01D71/06—Organic material
    • B01D71/76—Macromolecular material not specifically provided for in a single one of groups B01D71/08 - B01D71/74
    • B01D71/78—Graft polymers
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D2323/00—Details relating to membrane preparation
    • B01D2323/02—Hydrophilization
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D2323/00—Details relating to membrane preparation
    • B01D2323/38—Graft polymerization
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D71/00—Semi-permeable membranes for separation processes or apparatus characterised by the material; Manufacturing processes specially adapted therefor
    • B01D71/06—Organic material
    • B01D71/44—Polymers obtained by reactions only involving carbon-to-carbon unsaturated bonds, not provided for in a single one of groups B01D71/26-B01D71/42
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D71/00—Semi-permeable membranes for separation processes or apparatus characterised by the material; Manufacturing processes specially adapted therefor
    • B01D71/06—Organic material
    • B01D71/66—Polymers having sulfur in the main chain, with or without nitrogen, oxygen or carbon only
    • B01D71/68—Polysulfones; Polyethersulfones

Definitions

  • the present invention relates to a semipermeable asymmetric hollow fiber membrane, the membrane material being a graft copolymer of at least one hydrophobic polymer and at least one hydrophilic polymer.
  • the invention also relates to processes for the preparation of said membranes, devices comprising said membranes, and the use of said membranes in hemodialysis, hemodiafiltration or hemofiltration of blood as well as in bioprocessing, plasma fractionation and the preparation of protein solutions.
  • EP 0 305 787 Al discloses a permselective asymmetric mem ⁇ brane suitable for hemodialysis, hemodiafiltration and hemofiltration of blood, comprised of a hydrophobic first polymer, e.g. polyamide, a hydrophilic second polymer, e.g. polyvinylpyrrolidone, and suitable additives.
  • the membrane has a three-layer structure, comprising a first layer in the form of dense, rather thin skin, responsible for the sieving properties, a second layer in the form of a sponge structure, having a high diffusive permeability and serving as a support for said first layer, and a third layer in the form of a finger structure, giving the membrane mechanical stability .
  • EP 2 113 298 Al discloses a semipermeable asymmetric hollow fiber membrane based on polyethersulfone or polysulfone and a blend of low and high molecular weight PVP .
  • the membrane is suitable for hemodialysis, hemofiltration or hemodiafil- tration.
  • the membrane is further characterized by a four- layer structure.
  • the inner layer of the four-layer structure i.e. the blood contacting layer and the inner surface of the hollow filtration membrane, is a separation layer in the form of a dense layer having a thickness of less than 1 ⁇ and a pore size in the nano-scale range.
  • the next layer in the hollow fiber membrane has the form of a sponge structure.
  • the third layer has the form of a finger struc- ture .
  • the fourth layer is the outer layer with the outer surface.
  • the membrane has a wall thickness of between 20 and 60 ⁇ .
  • EP 2 365 022 Al discloses graft copolymers of at least one hydrophobic polymer and of at least one hydrophilic polymer formed by reactive blending of the at least one hydrophobic polymer and of the at least one hydrophilic polymer.
  • the copolymer is prepared by reactive blending in an extruder at a temperature in the range of from 280 to 350°C.
  • the present invention provides membranes made of novel graft copolymers, in particular semipermeable asymmetric hollow fiber membranes suitable for, e.g., hemodialysis, hemodiafiltration or hemofiltration of blood, as well as in bioprocessing, plasma fractionation and the preparation of protein solutions.
  • a semipermeable asymmetric hollow fiber membrane made of a graft copolymer of at least one polysulfone or polyethersulfone and at least one polyvinylpyrrolidone is provided.
  • the invention relates to a process for preparing the semipermeable asymmetric membrane of the invention.
  • the invention relates to a de ⁇ vice comprising the semipermeable asymmetric membrane of the invention.
  • Figure 1 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 3.
  • Figure 2 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 4.
  • Figure 3 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 5.
  • Figure 4 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 7.
  • Figure 5 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 8.
  • Figure 6 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 9.
  • Figure 7 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 10.
  • Figure 8 shows scanning electron micrographs (SEM) of a hollow fiber membrane produced according to Example 11. Detailed Description
  • the semipermeable asymmetric membrane of the invention is made of a graft copolymer of at least one polysulfone or polyethersulfone and at least one polyvinylpyrrolidone.
  • the graft polymer comprises 50 to 99 wt%, for instance 90 to 99 wt%, or 95 to 99 wt%, based on the total weight of the graft copolymer, of the at least one polysulfone or polyethersulfone, and 1 to 50 wt%, for instance, 1 to 10 wt%, or 1 to 5 wt%, based on the total weight of the graft copolymer, of the at least one polyvi ⁇ nylpyrrolidone .
  • a polysulfone having a weight average molecular weight of from 40,000 to 100,000 g/mol, for instance, 70,000 to 85,000 g/mol is used as a starting material.
  • suitable polysulfones are available from Solvay S.A., under the trade name Udel ® P- 1700 NT LCD, Udel ® P-1800, Udel ® P-3500 NT LCD, and Udel ® P- 1835, or from BASF S.E., under the trade name Ultrason ® S 6010.
  • a polyethersulfone hav ⁇ ing a weight average molecular weight of from 30,000 to 80,000 g/mol, for instance, from 40,000 to 60,000 g/mol is used as a starting material.
  • suitable polyeth ⁇ ersulfones are available from BASF S.E., under the trade name Ultrason ® E 6020 P, or from Solvay S.A., under the trade name Gafone ® 3000P, Gafone ® 3100P and Gafone ® 3200P.
  • a polyvinylpyrrolidone having a number average molecular weight of from 10,000 to 500,000 g/mol and a weight average molecular weight of from 40,000 to 2,500,000 g/mol is used as a starting material.
  • Examples include a polyvinylpyrrolidone having a number av- erage molecular weight of from 10,000 to 20,000 g/mol and a weight average molecular weight of 40,000 to 60,000 g/mol, a polyvinylpyrrolidone having a number average molecular weight of from 150,000 to 500,000 g/mol and a weight aver- age molecular weight of 700,000 to 2,500,000 g/mol, a poly ⁇ vinylpyrrolidone having a number average molecular weight of from 200,000 to 400,000 g/mol and a weight average mo ⁇ lecular weight of 900,000 to 2,000,000 g/mol, and a polyvi ⁇ nylpyrrolidone having a number average molecular weight of from 200,000 to 300,000 g/mol and a weight average molecu ⁇ lar weight of 900,000 to 1,200,000 g/mol.
  • a mixture of a polyvinylpyrrolidone having a mo ⁇ lecular weight of less than 100,000 g/mol and a polyvi ⁇ nylpyrrolidone of at least 100,000 g/mol is used as a starting material.
  • suitable polyvinylpyrrolido ⁇ nes are available from BASF S.E., under the trade name Lu- vitec ® .
  • An example of a suitable polyvinylpyrrolidone hav ⁇ ing a molecular weight of less than 100,000 g/mol is avail ⁇ able under the trade name Luvitec ® K30.
  • suit- able polyvinylpyrrolidones having a molecular weight of at least 100,000 g/mol are available under the trade name Lu- vitec ® K85 or Luvitec ® K90, respectively.
  • the graft copolymer is formed by reactive blending of at least one polysulfone or polyethersulfone and at least one polyvinylpyrrolidone in an extruder, e.g. a co-rotating twin screw extruder having three to five mixing zones and a ratio L/D (length to di ⁇ ameter) in the range of from 20 to 45, e.g., from 32 to 40.
  • an extruder e.g. a co-rotating twin screw extruder having three to five mixing zones and a ratio L/D (length to di ⁇ ameter) in the range of from 20 to 45, e.g., from 32 to 40.
  • the weight ratio of the at least poly ⁇ sulfone and/or polyethersulfone to the at least one polyvi ⁇ nylpyrrolidone in the reaction mixture fed to the extruder is in the range of from 50:50 to 95:5, for instance, from 70:30 to 90:10.
  • the reaction mixture does not contain a polymerization initiator.
  • reactive blending is performed in the presence of air. In one em- bodiment of the process, air or oxygen is introduced into the extruder during reactive blending.
  • a polymerization initiator is added to the reaction mixture.
  • suitable initiators are 2 , 3-dimethyl-2 , 3-diphenyl butane, 3, 4-dimethyl-3, 4- diphenyl butane, tert. -butyl hydro peroxide, or polycumene.
  • concentration of the polymerization initiator generally is in the range of from 0.08 to 5 wt% of the total weight of the reaction mixture, for instance from 0.15 to 0.5 wt%, relative to the total weight of the reaction mixture.
  • the temperature in the mixing zones of the extruder is in the range of from 250°C to 350°C, for instance, from 280 to 350°C, or from 300°C to 320°C.
  • the dwell time of the reaction mixture in the extruder is in the range of from 5 to 10 minutes, for instance, from 6 to 8 min.
  • the reaction mixture leaving the extruder is solidified and subsequently can be further processed.
  • the strand of extrudate leaving the extruder is conducted through a cooling bath to solidify the polymer.
  • the cooling bath contains water.
  • the strand of extrudate can be cut or granulated to produce beads or granules.
  • the beads or granules formed are subsequently dried.
  • the product obtained by the reactive blending is used without further purification.
  • the extrudate can be dissolved in a suitable sol ⁇ vent to produce a polymer solution.
  • suitable solvents include dichloromethane, N-methylpyrrolidone
  • NMP dimethylacetamide
  • DMAC dimethylacetamide
  • DMF dimethylformamide
  • DMSO dimethylsulfoxide
  • NMP is used to dissolve the extrudate.
  • the product ob ⁇ tained by the reactive blending process is further proc ⁇ essed to remove unreacted starting materials and by ⁇ products.
  • the extrudate is dissolved in a solvent and subsequently precipitated by addition of a precipitation medium.
  • suitable solvents include dichloromethane, N-methylpyrrolidone (NMP) and dimethyl ⁇ acetamide (DMAC) .
  • suitable precipitation media include water and alcohols like methanol or ethanol.
  • residual amounts of soluble polyvinylpyrroli- done are removed from the precipitate by extraction.
  • suitable extraction media include methanol, etha ⁇ nol, tetrahydrofurane, and supercritical carbon dioxide.
  • the precipitate is extracted with methanol.
  • the precipitate is subsequently dried to remove volatiles.
  • the graft copolymer is dis ⁇ solved in a suitable solvent.
  • suitable solvents include dichloromethane, dimethylsulfoxide, N-methylpyrro- lidone (NMP) , N-ethylpyrrolidone (NEP) , N-octylpyrrolidone (NOP) , dimethylformamide (DMF) , dimethylsulfoxide (DMSO) and dimethylacetamide (DMAC) .
  • NMP N-methylpyrro- lidone
  • NEP N-ethylpyrrolidone
  • NOP N-octylpyrrolidone
  • DMF dimethylformamide
  • DMSO dimethylsulfoxide
  • DMAC dimethylacetamide
  • the prod ⁇ uct is dissolved in NMP.
  • the product is dissolved in DMAC.
  • a membrane is formed by a solvent phase inversion spinning process, com ⁇ prising the steps of a) dissolving the graft copolymer in at least one sol ⁇ vent to form a graft copolymer solution; b) extruding said graft copolymer solution through an outer ring slit of a nozzle with two concentric open ⁇ ings into a precipitation bath; simultaneously c) extruding a center fluid through the inner opening of the nozzle; and thereafter d) washing the membrane obtained; e) drying said membrane and, optionally, sterilizing
  • the copolymer solution contains 10-40 wt%, e.g., 20 to 30 wt% or 25 to 35 wt%, of graft copolymer, and 53-90 wt% of solvent;
  • the cen ⁇ ter liquid contains 20-60 wt%, e.g., 20 to 50 wt%, of wa ⁇ ter, 40-80 wt%, e.g.
  • the precipitation bath contains 20-100 wt% of water and 0-80 wt% of a solvent and has a temperature within the range of from 5 to 60 °C; and the distance be ⁇ tween the discharge outlet of the hollow fiber spinning nozzle and the surface of the precipitation bath (falling height) is within the range of from 0 to 100 cm.
  • the hollow fiber spinning nozzle (die, spinneret) is held at a temperature within the range of from 20 to 70°C, e.g., within the range of from 25 to 55°C, or even from 30 to 45°C.
  • the spinning speed (v ab ) of the hollow fiber membrane is 5-60 m/min, e.g., 15- 45 m/min.
  • the polymer solution has a dynamic viscosity, measured at 22°C, of from 100 to 20,000 mPa*s (determined according to DIN ISO 1628-1) .
  • the center fluid or bore liquid which is used for preparing the membrane according to the invention comprises at least one of the solvents selected from the group consisting of N-methylpyrrolidone (NMP) , N-ethylpyrrolidone, N-octyl- pyrrolidone, dimethylacetamide (DMAC) , dimethylsulfoxide
  • NMP N-methylpyrrolidone
  • DMAC dimethylacetamide
  • the center fluid additionally com ⁇ prises a further additive to modify the surface of the mem ⁇ brane in order to further increase the performance of the membrane.
  • the amount of the additive in the center fluid is from 0 to 5 wt%, e.g., from 0.1 to 0.5 wt%, based on the total weight of the cen ⁇ ter fluid.
  • suitable additives include hyaluronic acid and zwitterionic polymers as well as copolymers of a vinyl po- lymerizable monomer having a zwitterion in the molecule and another vinyl polymerizable monomer.
  • zwitterionic (co) polymers include phosphobetains , sulfobetains , and carboxybetains .
  • the polymer solution com ⁇ ing out through the outer slit opening of the spinneret is guided through a spinning shaft with controlled atmosphere.
  • the spinning shaft is held at a temperature within the range of from 2 to 90 °C, e.g., within the range of from 25 to 70°C, or from 30 to 60°C.
  • the precipitating fiber is exposed to a humid steam/air mixture comprising a solvent in a content of from 0 to 10 wt%, for instance, from 0 to 5 wt%, or from 0 to 3 wt%, related to the water content.
  • the temperature of the humid steam/air mixture is at least 15°C, preferably at least 30°C, and at most 75°C, e.g. not higher than 62°C.
  • the relative humidity in the humid steam/air mix ⁇ ture is from 60 to 100%.
  • the effect of the solvent in the temperature-controlled steam atmosphere is to control the speed of precipitation of the fibers.
  • the outer surface will obtain a denser surface, and when more solvent is used, the outer surface will have a more open structure.
  • the membrane is washed in at least one water bath. In one embodiment of the process, at least four water baths are used to wash the membrane .
  • the membrane is then dried at temperatures in the range of from 150 to 280°C, e.g. in the range of from 180 to 260°C. Such drying will provide for an adequate evaporation of water and a defined shrinkage of pores.
  • the membrane can be dried discontinuously or continuously, the latter also be ⁇ ing called "online-drying". In the online-drying process, the membrane is continuously fed to a dryer.
  • the drying can be effected by any method known in the art. For instance, the membrane can be dried in a convection oven or by a stream of hot air, e.g. from a nozzle, by contact with a hot surface, or by irradiation, e.g. with infra-red or mi- cro-wave radiation.
  • the asymmetric hollow fiber membrane according to the pre ⁇ sent invention has a hydrophilic, spontaneously wettable membrane structure, low fouling properties for long term stable filtration, and low protein adsorption.
  • the asymmetric hollow fiber membrane further has smooth surfaces which avoids or minimizes hemolysis during blood processing.
  • the membrane exhibits high biocompatibility, low or no comple ⁇ ment activation and low thrombogenicity .
  • the hollow fiber membrane has an inner diameter in the range of from 100 to 700 ⁇ .
  • the membrane of the present invention has an inner diameter in the range of from 150 to 220 ⁇ ; e.g. for use in haemodi- alysis.
  • the membrane of the present invention has an inner diameter in the range of from 300 to 350 ⁇ ; e.g. for use in plasma separation.
  • the membrane of the present invention has an inner diameter in the range of from 100 to 150 ⁇ ; e.g. for membranes having the selective layer on the outside.
  • the membrane of the present in ⁇ vention has an inner diameter in the range of from 300 to 700 ⁇ and a wall thickness in the range of from 60 to 100 ⁇ , e.g. for bioprocessing membranes.
  • the hollow fiber membrane has a wall thickness in the range of 5 to 150 ⁇ , for instance from 5 to 50 ⁇ , from 5 to 25 ⁇ , or from 5 to 18 ⁇ .
  • the membrane of the in- vention is a hollow fiber membrane having a three-layer structure .
  • the first layer of the three-layer structure i.e. the blood contacting layer and the inner surface of the hollow fiber membrane, is a separation layer in the form of a dense layer.
  • the layer has a thickness of less than 1 ⁇ .
  • the next layer in the hollow fiber membrane has the form of a sponge structure and, in one embodiment of the present invention, a thickness in the range of from 1 to 50 ⁇ , e.g. 1 to 20, or 1 to 10, or 1 to 5 ⁇ , and serves as a support for the first layer.
  • the third layer in this embodiment of the present invention is the outer layer, which is characterized by a homogeneous and open pore structure with a defined surface roughness. In one embodiment, this third layer has a thickness in the range of from 1 to 50 ⁇ , e.g. 1 to 20, or 1 to 10, or 1 to 5 ⁇ .
  • the membrane of the invention is a hollow fiber membrane having a four-layer structure.
  • the first layer of the four-layer structure i.e. the blood contacting layer and the inner surface of the hollow fiber membrane, is a separation layer in the form of a dense layer having, in one embodiment, a thickness of less than 1 ⁇ and a pore size in the nano-scale range.
  • the next layer in the hollow fiber membrane has a sponge structure and, in one embodiment of the present invention, a thickness in the range of from 1 to 15 ⁇ , e.g. 1 to 10, or 1 to 5 ⁇ , and serves as a support for said first layer.
  • the third layer has the form of a finger structure. It pro ⁇ vides for mechanical stability on the one hand; on the other hand it has, through the high void volume, a very low resistance of transport of molecules through the membrane.
  • the third layer has a thickness of from 20 to 60 ⁇ .
  • the third layer has a thickness of from 5 to 25, or even 5 to 10 ⁇ .
  • the fourth layer in this embodiment of the present inven ⁇ tion is the outer layer, which is characterized by a homo ⁇ geneous and open pore structure with a defined surface roughness. In one embodiment, this fourth layer has a thickness in the range of from 1 to 10 ⁇ , or 1 to 5 ⁇ .
  • the openings of the pores are in the size range of from 0.5 to 3 ⁇ , further the number of pores on the outer surface is in the range of from 10,000 to 150,000 pores per mm 2 , for example in the range of from 18,000 to 100,000 pores per mm 2 , or even in the range of from 20,000 to 100,000 pores per mm 2 .
  • the selective layer i.e. the layer with the narrowest average pore size, is the inner surface of the hollow fiber membrane.
  • the selective layer is the outer surface of the hollow fiber membrane.
  • the membrane has a three- or four-layer structure as described before, but with reversed sequence of the layers.
  • Membranes having the outer surface as se ⁇ lective layer are disclosed in EP 2 228 126 Al, incorpo ⁇ rated herein by reference.
  • the membranes of the invention have a layer structure similar to one of the structures described in EP 2 228 126 Al .
  • the membrane is a nanofiltration mem ⁇ brane and the selective separation layer has a number average pore diameter in the range of from 1 to less than 10 nm.
  • the membrane is a ultrafiltration membrane and the selective separation layer has a number average pore diameter in the range of from 0.01 to less than 0.1 ⁇ .
  • the membrane is a microfiltration membrane and the selective separation layer has a number average pore diameter in the range of from 0.1 to 0.5 ⁇ .
  • the membrane is a plasma sepa ⁇ ration membrane and the selective separation layer has a number average pore diameter of more than 0.5 ⁇ .
  • the copolymer of the present invention has the advantage that it enables the formation of membranes with smaller wall thicknesses or higher mechanical stability, respec ⁇ tively, than the membranes produced starting from blends of polyethersulfone or polysulfone and polyvinylpyrrolidone.
  • a further advantage of the copolymer is the reduced leach ⁇ ing of polyvinylpyrrolidone from the membrane during the washing step after formation of the membrane than in the respective step starting from a polymer blend. Hence, less polyvinylpyrrolidone has to be employed for membrane forma- tion, and less polyvinylpyrrolidone is lost in the washing step, respectively.
  • Another aspect of the invention is a diffusion and/or fil- tration device comprising the membrane of the invention.
  • Such devices are dialyzers, hemofilters, ul- trafilters and plasmafliters .
  • Such devices generally con ⁇ sist of a casing comprising a tubular section with end caps capping the mouths of the tubular section.
  • a bundle of hol- low fiber membranes is usually arranged in the casing in a way that a seal is provided between the first flow space formed by the fiber cavities and a second flow space sur ⁇ rounding the membranes on the outside. Examples of such de ⁇ vices are disclosed in EP 0 844 015 A2, EP 0 305 687 Al, and WO 01/60477 A2, all incorporated herein by reference.
  • the separation material of the invention is used in plasmapheresis. In a further embodiment of the invention, the separation material is used in hemodialysis, hemodiafiltration or hemofiltration applications.
  • the separation material of the invention can be used for these purposes instead of conventional membranes, but in a similar manner. The person skilled in the art will easily derive the necessary modus operandi.
  • Another aspect of the invention is the use of the membrane of the invention in bioprocessing, plasma fractionation and the preparation of protein solutions.
  • the membrane of the invention can be used for these purposes instead of mem- branes conventionally used for these purposes.
  • the person skilled in the art will easily derive a suitable modus op ⁇ erandi for the intended application.
  • the extrudate was dissolved in NMP to produce a 10% (w/w) solution and precipitated from the solution by the addition of methanol.
  • the precipitate was transferred to a Soxhlet extractor, extracted with methanol for 65 hrs to remove any residual PVP not chemically bound in the graft copolymer, and subsequently dried.
  • Polysulfone/polyvinylpyrrolidone copolymers were dissolved in CDC1 3 . 1 H-NMR spectra were recorded and PVP content was calculated from the integrals of the signal at 3.0-3.5 ppm (2H) for polyvinylpyrrolidone, 7.84 ppm (4H) for polysulfone and the molecular weights of the respective repeating units (polysulfone 442.53 g/mol; polyvinylpyrrolidone 111.14 g/mol) .
  • Polyethersulfone/polyvinylpyrrolidone copolymers were dissolved in d 6 -DMSO. 1 H-NMR spectra were recorded and PVP content was calculated from the integrals of the signal at 2.85-3.35 ppm (2H) for polyvinylpyrrolidone, 8.0 ppm (4H) for polyethersulfone and the molecular weights of the respective repeating units (polyethersulfone 232.26 g/mol;
  • the fibers were potted with polyurethane . After the polyurethane had hardened, the potted membrane bundle was cut to open the fibers and stored dry before it was used for the different performance tests.
  • the mini-modules ensure protection of the fibers and were used for steam-sterilization of the fiber.
  • the manufacturing of the mini-modules differs in the
  • n amount of fibers
  • the fiber bundle was cut to a defined length of 20 cm
  • the fiber bundle was transferred into a housing before melting process
  • a filter is characterized by a cylindrical housing with two connectors for the dialyzing fluid and caps applied on both ends, each with one centered blood connector.
  • the manufacturing process (after winding of the fibers) comprises the following main steps :
  • the membrane bundle was wetted for thirty minutes before the Lp-test was performed. For this purpose, the membrane bundle was put in a box containing 500 ml of ultrapure water. After 30 minutes, the membrane bundle was transferred into the testing system.
  • the testing system consisted of a water bath that was maintained at 37 °C and a device where the membrane bundle was mounted. The membrane bundle was located
  • an integrity test of the membrane bundle and the test system was carried out in advance.
  • the integrity test was performed by pressing air through the membrane bundle that was closed on one side of the bundle. In the test, air bubbles indicate a leakage of the membrane bundle or the test device. If bubbles occur, it has to be checked whether the leakage is due to an incorrect mounting of the membrane bundle in the test device or if a real membrane leakage is present. The membrane bundle was discarded when a leakage of the membrane was detected.
  • the pressure applied in the integrity test has to be at least the same value as the pressure applied during the determination of the hydraulic permeability in order to ensure that no leakage can occur during the measurement of the hydraulic permeability.
  • the selectivity of a membrane was determined by sieving coefficient measurements.
  • the sieving coefficient of the particular protein was obtained as follows: The protein solution was maintained at a temperature of 37 °C ⁇ 1°C and pumped through the testing device (hand bundles, mini-modules or filters) under defined conditions (blood flow (Q B ) , TMP and filtration rate (UF) ) . Then, the concentration of the protein in the feed (in) , in the retentate (r) and in the filtrate (f) was determined and the sieving coefficient (SC) was calculated according to the following equation (2) :
  • the Sieving Coefficient experiments in aqueous solution of myoglobin and albumin were performed using two different experimental set-ups with separate solutions. First, the sieving coefficient of myoglobin was determined. Then the sieving coefficient of albumin was determined.
  • the concentration of myoglobin in the PBS buffer was 100 mg/1.
  • the expiry date of the aqueous solution is between 4 and 8 weeks. The solution has to be stored in the
  • n amount of fibers
  • the shear rate was set to 500 s -1 and the intrinsic flow rate was deter- mined to be 0.38*10 "04 cm/s .
  • the first samples were taken after 15 minutes (pool, reten- tate, and filtrate) and a second time after 60 min. At the end, the test-bundle was rinsed for some minutes with PBS- buffer, and then the test was stopped.
  • the SC-test of albumin was performed. 60 g of albumin were dissolved in PBS-buffer and the experiment was run re-circulating, the albumin solution being slowly stirred by a magnetic bar stirrer.
  • the Q B was calculated according to equation (3) , a fixed TMP of 400 mmHg was set and the UF as well as the retentate flow was a result of the test conditions and the membrane permeability properties. After 15 minutes, the flow was switched to single-pass and samples (pool, retentate, filtrate) were taken. After the SC-test the test-bundle was rinsed once more with PBS-buffer and used to perform a second Lp-test in order to get an indication of the
  • the dynamic viscosity ⁇ of the polymer solutions was deter ⁇ mined according to DIN ISO 1628-1 at a temperature of 22 °C using a capillary viscosimeter (ViscoSystem ® AVS 370,
  • PSU polysulfone Udel ® P-3500 NT LCD, Solvay S.A.;
  • PVP-K30 polyvinylpyrrolidone Luvitec ® K30, BASF S.E.;
  • the polymers were dried overnight at 80 °C before use.
  • PSU and PVP-K30 were fed to the extruder at a weight ratio of 90:10; with addition of 0.30 wt%, relative to the total weight of polymer, of DMDPB; content of chemically bound PVP in the product was 2.0 wt%.
  • Example 2
  • the solution had a dynamic vis ⁇ cosity of 710 mPa*s at 22°C.
  • Example 2 The solution of Example 2 was used to produce hollow fiber membranes under different spinning conditions, as summa ⁇ rized in Table 1.
  • Example 3-5 the precipitation bath had a temperature of 18 °C.
  • the active separation layer of the membranes was at the inner side. Scanning Electron Micrographs (SEM) of the fibers of Examples 3-5 are shown in Figures 1-3.
  • a solution comprising 25 wt% of the graft copolymer ob- tained in Example 1 and 75 wt% of NMP was prepared by stir ring the graft copolymer in the solvent at 60 °C overnight.
  • the solution had a dynamic viscosity of 7,625 mPa*s at 22°C. Examples 7-11
  • Example 6 The solution of Example 6 was used to produce hollow fiber membranes under different spinning conditions, as summa ⁇ rized in Table 3.
  • Table 3 Spinning parameters for Examples 7-11.

Abstract

La présente invention concerne une fibre creuse à membrane asymétrique semi-perméable faite d'une substance en polymère greffe comprenant au moins un polymère hydrophobe et au moins un polymère hydrophile. L'invention concerne également des procédés destinés à l'élaboration desdites fibres, des dispositifs comprenant lesdites fibres, et l'utilisation desdites fibres pour l'hémodialyse, l'hémodiafiltration, ou l'hémofiltration du sang, ainsi que pour un traitement biologique, le fractionnement du plasma, et l'élaboration de solutés de protéines.
PCT/EP2012/067353 2011-09-08 2012-09-06 Fibre creuse WO2013034611A1 (fr)

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DE102016012722A1 (de) 2016-10-24 2018-04-26 Fresenius Medical Care Deutschland Gmbh Verfahren zur Bestimmung einer Permeationseigenschaft von Hohlfasermembranen
DE102016012730A1 (de) 2016-10-24 2018-04-26 Fresenius Medical Care Deutschland Gmbh Verfahren zur Bestimmung einer Permeationseigenschaft von Hohlfasermembranen
WO2018104498A2 (fr) 2016-12-09 2018-06-14 Fresenius Medical Care Deutschland Gmbh Membrane à fibres creuses ayant de meilleures performances de séparation et fabrication d'une membrane à fibres creuses ayant de meilleures performances de séparation
US10851241B2 (en) 2014-11-19 2020-12-01 Cytiva Sweden Ab Zwitterion-functionalized multicomponent copolymers and associated polymer blends and membranes
WO2021023711A1 (fr) 2019-08-06 2021-02-11 Solvay Specialty Polymers Usa, Llc Membrane et polymère pour sa fabrication
RU2747972C2 (ru) * 2016-09-30 2021-05-18 Торэй Индастриз, Инк. Модуль разделительной мембраны
WO2024068441A1 (fr) * 2022-09-26 2024-04-04 Solvay Specialty Polymers Usa, Llc Copolymères de polyaryléther greffés

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EP2845641B1 (fr) 2013-09-05 2018-05-09 Gambro Lundia AB Membranes permsélectives asymétriques avec polyvinylpyrrolidone à haut poids moléculaire, leur préparation et leur utilisation
KR102189592B1 (ko) 2015-11-20 2020-12-11 이엠디 밀리포어 코포레이션 향상된 안정도의 필터 완전성 시험
EP3560577A1 (fr) 2018-04-25 2019-10-30 Gambro Lundia AB Appareil et procédé pour tester l'intégrité d'une membrane d'ultrafiltration
EP3845301A1 (fr) 2019-12-31 2021-07-07 Gambro Lundia AB Procédé de fabrication d'un filtre stérilisant

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DE102016012722A1 (de) 2016-10-24 2018-04-26 Fresenius Medical Care Deutschland Gmbh Verfahren zur Bestimmung einer Permeationseigenschaft von Hohlfasermembranen
CN109890485A (zh) * 2016-10-24 2019-06-14 费森尤斯医疗护理德国有限责任公司 用于确定中空纤维膜束的渗透性能的方法
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WO2018104498A2 (fr) 2016-12-09 2018-06-14 Fresenius Medical Care Deutschland Gmbh Membrane à fibres creuses ayant de meilleures performances de séparation et fabrication d'une membrane à fibres creuses ayant de meilleures performances de séparation
DE102016224627A1 (de) 2016-12-09 2018-06-14 Fresenius Medical Care Deutschland Gmbh Hohlfasermembran mit verbesserter Trennleistung und Herstellung einer Hohlfasermembran mit verbesserter Trennleistung
US11478759B2 (en) 2016-12-09 2022-10-25 Fresenius Medical Care Deutschland Gmbh Hollow fibre membrane with improved separating efficiency, and production of a hollow fibre membrane with improved separating efficiency
JP7187455B2 (ja) 2016-12-09 2022-12-12 フレゼニウス メディカル ケア ドイッチェランド ゲゼルシャフト ミット ベシュレンクテル ハフツング 改善された分離効率を有する中空糸膜、および改善された分離効率を有する中空糸膜の生成
JP2020513308A (ja) * 2016-12-09 2020-05-14 フレゼニウス メディカル ケア ドイッチェランド ゲゼルシャフト ミット ベシュレンクテル ハフツング 改善された分離効率を有する中空糸膜、および改善された分離効率を有する中空糸膜の生成
WO2021023711A1 (fr) 2019-08-06 2021-02-11 Solvay Specialty Polymers Usa, Llc Membrane et polymère pour sa fabrication
WO2024068441A1 (fr) * 2022-09-26 2024-04-04 Solvay Specialty Polymers Usa, Llc Copolymères de polyaryléther greffés

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